Method of fabricating a low crystallinity poly(l-lactide) tube

ABSTRACT

Methods of fabricating a low crystallinity polymer tube for polymers subject to strain-induced crystallization. The low crystallinity tube may be further processed to make an implantable medical device.

This application is a continuation of U.S. patent application Ser. No.12/550,153 filed Aug. 28, 2009, and is incorporated by reference herein.

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention relates to methods of manufacturing polymeric medicaldevices, in particular, stents.

2. Description of the State of the Art

The discussion that follows is intended solely as background informationto assist in the understanding of the invention herein; nothing in thissection is intended to be, nor is it to be construed as, prior art tothis invention.

Until the mid-1980s, the accepted treatment for atherosclerosis, i.e.,narrowing of the coronary artery(ies) was coronary by-pass surgery.While effective and having evolved to a relatively high degree of safetyfor such an invasive procedure, by-pass surgery still involves seriouspotential complications and in the best of cases, an extended recoveryperiod.

With the advent of percutaneous transluminal coronary angioplasty (PTCA)in 1977, the scene changed dramatically. Using catheter techniquesoriginally developed for heart exploration, inflatable balloons wereemployed to re-open occluded regions in arteries. The procedure wasrelatively non-invasive, took a very short time compared to by-passsurgery and the recovery time was minimal. However, PTCA brought with itanother problem, elastic recoil of the stretched arterial wall whichcould undo much of what was accomplished and, in addition, failed tosatisfactorily ameliorate another problem, restenosis, the re-cloggingof the treated artery.

The next improvement, advanced in the mid-1980s was use of a stent toscaffold the vessel wall in place after PTCA. This, for all intents andpurposes, put an end to recoil, but did not entirely resolve the issueof restenosis. That is, prior to the introduction of stents, restenosisoccurred in from 30-50% of patients undergoing PTCA. Stenting reducedthis to about 15-20%, much improved, but still more than desirable.

In 2003, drug-eluting stents or DESs were introduced. The drugsinitially employed with the DES were cytostatic compounds, compoundsthat curtailed the proliferation of cells that resulted in restenosis.The occurrence of restenosis was thereby reduced to about 5-7%, arelatively acceptable figure. Today, the DES is the default industrystandard for the treatment of atherosclerosis and is rapidly gainingfavor for treatment of stenoses of blood vessels other than coronaryarteries such as peripheral angioplasty of the superficial femoralartery.

The next generation of stents will be those designed to bebiodegradable. Although bioerodable metals may be used, biodegradablepolymers are often used for fabrication of such a stent. However, thereare potential shortcomings in the use of polymers as a material forimplantable medical devices, such as stents. The strength to weightratio of polymers is usually smaller than that of metals. Also, certainpolymers have low toughness, i.e. are brittle. Semicrystalline polymersin particular are useful as stent material. However, they must beprocessed in a manner that provides high strength and fracturetoughness.

SUMMARY OF THE INVENTION

Various embodiments of the present invention include a method offabricating an implantable medical device, such as a stent. The methodincludes, but is not limited to, performing the following operations:heating and mixing a polymer or a polymer blend, optionally with othermaterials, in an extruder to form a polymer melt; forming a tube fromthe polymer melt using the extruder and a die assembly in which thepolymer melt flows in a spiral motion through at least part of the dieassembly, and wherein the crystallinity of the polymer in the formedtube is not more than 5%; processing the polymer tube at a temperaturebelow the melting temperature (T_(m)) of the polymer to increase theradial strength of the polymer tube and increase the crystallinity ofthe polymer tube between about 20% and about 50%; and forming a stentfrom the processed polymer tube.

In some embodiments, the spiral flow results from the die assembly used.The die assembly comprises a passage way from inlet to outlet and atleast a portion of the passage way is formed by cooperative engagementof first and second conical surfaces, or substantially conical surfaces.The spiral flow of the polymer melt results from flow through aplurality of grooves in at least one of the conical surfaces, and atleast one of the grooves forms a portion of a conical helix.

In some embodiments, forming an implantable medical device, such as astent, from the polymer tube includes radially expanding the polymertube at a temperature between the glass transition temperature (T_(g))and the melting temperature of the polymer, and forming a stent from theprocessed tube.

In some embodiments, the polymer is poly(L-lactide), and the polymertube is processed by radial expansion at a temperature in the range of60° C. to 100° C.

Other methods of fabricating an implantable medical device areencompassed by the various embodiments of the present invention. Themethods include, but are not limited to, the following operations:heating and mixing a polymer or a polymer blend, optionally with othermaterials, in an extruder to form a polymer melt; and forming a tubefrom the polymer melt such that the polymer of the formed tube has acrystallinity of not more than 5%. The tube is formed using the extruderand a die assembly wherein when the polymer melt has a velocitycomponent in the azimuthal direction during at least a portion of thetime that the polymer flows through an annular portion of the dieassembly.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 depicts a stent.

FIG. 2 depicts a flow chart of a conventional extrusion process.

FIG. 3 depicts a die assembly useful in performing the methods of thepresent invention

FIG. 4 depicts a top view of a representative inlet to a die assembly.

FIG. 5 depicts spiral grooves in part of a die assembly useful inperforming the methods of the present invention.

FIGS. 6A and 6B depict helices in cartesian and cylindrical coordinates.

FIG. 7 depicts a conical helix on the face of a cone.

FIGS. 8A and 8B depict top-views illustrating aspects of a part of a dieassembly useful in performing the methods of the present invention.

FIGS. 9A, 9B, and 9C depict the cross-section of grooves in part of adie assembly useful in performing the methods of the present invention.

FIG. 10 depicts the vector components of the polymer melt velocity incylindrical coordinates.

FIG. 11 depicts the flow pattern of a polymer melt in a spiral groove.

FIG. 12 depicts the distribution of polymer melt around an annularpassage way of a die assembly.

DETAILED DESCRIPTION OF THE INVENTION

Use of the singular herein includes the plural and vice versa unlessexpressly stated to be otherwise. That is, “a” and “the” refer to one ormore of whatever the word modifies. For example, “a tube” includes onetube, two tubes, etc. Likewise, “a polymer” may refer to one, two ormore polymers, and “the polymer” may mean one polymer or a plurality ofpolymers. By the same token, words such as, without limitation, “tubes”and “polymers” would refer to one tube or polymer as well as to aplurality of tubes or polymers unless, again, it is expressly stated orobvious from the context that such is not intended.

As used herein, any ranges presented are inclusive of the end-points.For example, “a temperature between 10° C. and 30° C.” or “a temperaturefrom 10° C. to 30° C.” includes 10° C. and 30° C., as well as anytemperature in between.

As used herein, unless specifically defined otherwise, any words ofapproximation such as without limitation, “about,” “essentially,”“substantially” and the like mean that the element so modified need notbe exactly what is described but can vary from the description by asmuch as ±15% without exceeding the scope of this invention.

As used herein, the use of “preferred,” “preferably,” or “morepreferred,” and the like to modify an aspect of the invention refers topreferences as they existed at the time of filing of the patentapplication.

This invention relates to medical devices, and particularly, implantablemedical devices. Implantable medical devices include appliances that aretotally or partly introduced, surgically or medically, into a patient'sbody or by medical intervention into a natural orifice, and which areintended to remain there after the procedure. Examples of implantablemedical devices include, without limitation, implantable cardiacpacemakers and defibrillators; leads and electrodes for the preceding;implantable organ stimulators such as nerve, bladder, sphincter anddiaphragm stimulators, cochlear implants; prostheses, vascular grafts,self-expandable stents, balloon-expandable stents, stent-grafts, grafts,artificial heart valves, closure devices for patent foramen ovale,vascular closure devices, cerebrospinal fluid shunts, and intrauterinedevices.

More particularly, this invention is directed to stents, a type ofimplantable medical device. Although the discussion that follows focuseson a stent as an example of an implantable medical device, theembodiments described herein are easily applicable to other implantablemedical devices.

Stents are generally cylindrically shaped devices that function to holdopen, and sometimes expand, a segment of a blood vessel or otheranatomical lumen such as urinary tracts and bile ducts. A “lumen” refersto a cavity of a tubular organ such as a blood vessel. Stents are oftenused in the treatment of atherosclerotic stenosis in blood vessels.“Stenosis” refers to a narrowing or constriction of a bodily passage ororifice. “Restenosis” refers to the reoccurrence of stenosis in a bloodvessel or heart valve after it has been treated (as by balloonangioplasty, stenting, or valvuloplasty) with apparent success. Intreatment of stenosis, stents reinforce body vessels and preventrestenosis following angioplasty in the vascular system. In addition totreatment for coronary artery disease such as atherosclerosis andrestenosis, stents may be used for the maintenance of the patency of avessel in a patient's body when the vessel is narrowed or closed due todiseases or disorders including, without limitation, tumors (in, forexample, bile ducts, the esophagus, the trachea/bronchi, etc.), benignpancreatic disease carotid artery disease, peripheral arterial disease(PAD), and vulnerable plaque. For treatment of PAD, stents may be usedin peripheral arteries such as the superficial femoral artery (SFA). Useof stents in the SFA appears to be more challenging than in coronaryvessels and in other peripheral vascular beds, such as the iliac andcarotid arteries.

Stents are typically composed of scaffolding that physically holds openand, if desired, expands the wall of a passage way. FIG. 1 depicts anexample of a three-dimensional view of a stent 10. In some embodiments,a stent may include a body, backbone, or scaffolding having a pattern ornetwork of interconnecting structural elements or struts 15. In general,the body of a medical device may be the device in a functional form, butprior to the application of a coating or other material different fromthat of which the device body is formed. The embodiments disclosedherein are not limited to stents or to the stent pattern illustrated inFIG. 1. The structural pattern of the device, including a stent, can beof virtually any design.

A stent such as stent 10 may be fabricated from a polymeric tube, or asheet by rolling and bonding the sheet to form a tube. A tube or sheetcan be formed by extrusion or injection molding. A stent pattern, suchas the one pictured in FIG. 1, can be formed in a tube or sheet with atechnique such as laser cutting or chemical etching.

Typically, stents are capable of being compressed, or crimped, onto acatheter so that they can be delivered to, and deployed at, a treatmentsite. Delivery includes inserting the stent through small lumens using acatheter and transporting it to the treatment site. Deployment includesexpanding the stent to a larger diameter once it is at the desiredlocation.

The stent must be able to satisfy several mechanical requirements.First, the stent must be capable of withstanding the structural loads,namely radial compressive forces, imposed on the stent as it supportsthe walls of a vessel lumen. This requires a sufficient degree ofstrength and rigidity or stiffness. In addition to having adequateradial strength, the stent should be longitudinally flexible to allow itto be maneuvered through a tortuous path and to enable it to conform toa deployment site that may not be linear or may be subject to flexure.The material from which the stent is constructed must allow the stent toundergo expansion which typically requires substantial deformation ofportions of the stent. Once expanded, the stent must maintain its sizeand shape throughout its service life despite the various forces thatmay come to bear thereon, for example and without limitation, the cyclicloading induced by the beating heart. A stent must be capable ofexhibiting relatively high toughness or resistance to fracture. Forstents used in the SFA, the mechanical requirements can be higher thanfor stents in coronary arteries as the SFA is subjected to variousforces, such as compression, torsion, flexion, extension, andcontraction, which place a high demand on the mechanical performance ofimplants.

Although stents made of nonerodible metals and metal alloys have becomethe standard of care for treatment of artery disease, it is desirable tomake stents out of biodegradable polymers. In many treatmentapplications, the presence of a stent in a body is necessary for alimited period of time until its intended function of, for example,maintaining vascular patency and/or drug delivery is accomplished.Therefore, a device body, including the scaffolding of a stent, may befabricated from biodegradable, bioabsorbable, and/or bioerodablepolymers and can be configured to partially or completely erode awayafter the clinical need for them has ended.

The duration during which the device maintains luminal patency dependson the bodily disorder that is being treated. If a drug is included inthe device, the duration of drug delivery may be the same as or maydiffer from the duration during which luminal patency is maintained. Forexample, in treatments of coronary heart disease involving use of stentsin diseased vessels, the duration can be in a range from several monthsto a few years. The duration is typically up to about six months, twelvemonths, eighteen months, or two years. In some situations, the treatmentperiod can extend beyond two years. As another example, in treatments ofSFA, the duration can be in a range from one or two months to severalyears. For SFA, the duration is typically up to up to about six months,twelve months, eighteen months, or two years. Preferably luminal patencyis maintained for a time period between about 6 months and about 8months.

Although biodegradable polymers can de designed to erode away, as notedabove, one drawback of polymers as compared to metals and metal alloysis that the strength to weight ratio of polymers is usually smaller thanthat of metals. To compensate for this, a polymeric stent can requiresignificantly thicker struts than a metallic stent, which results in anundesirably large profile. One way of addressing the strength deficiencyof polymers is to process the polymer in a manner that improves itsstrength and toughness. The strength and toughness of a polymer is acomplex function of the morphology of the polymer, particularly if thepolymer is a semicrystalline polymer. Semicrystalline polymers with highstrength and toughness can be achieved by orienting the polymer chains,particularly in a biaxial orientation, having small crystalline domains,and a high crystal density.

Polymer chain orientation may be obtained by deforming the polymer.Deforming polymers tends to increase the strength along the direction ofdeformation (strain), which is believed to be due to the induced polymerchain orientation along the direction of deformation. For example, apolymer tube can be fabricated to obtain a biaxial orientation by bothaxial and radial deformation of the polymer tube. The radial expansionof a tube provides preferred circumferential polymer chain orientationin the tube, and stretching a tube provides preferred axial orientationof polymer chains in the tube. The ratio of radial to axial orientationmust be optimized for a particular stent design to obtain desirablemechanical properties.

As noted above, another way to improve fracture toughness is by reducingthe size of the polymer crystals and increasing the density of thenuclei from which the crystals grow. Smaller crystals lead to more tiechains between crystals, that is polymer chains that are part of bothcrystals. The amorphous regions between crystals contribute to strengthand fracture toughness. Also, crystals or crystalline regions actanalogously to physical cross-links and increase modulus. However, ifthe crystallinity is too high, then fracture toughness and elongationare reduced. Thus, some crystallinity is desirable, but not so much thatthe polymer becomes brittle. Many small crystalline regions arepreferable to fewer larger crystalline regions. A combination of highcrystal density and small crystal size is preferred.

Crystal size and density, as well as the total crystallinity, are aresult of the temperature and processing history of the polymer. For apolymer, crystallization generally tends to occur at temperaturesbetween the glass transition temperature, T_(g), and the meltingtemperature, T_(m), of the polymer. At temperatures close to T_(g) therate of crystal nucleation rate is greater then the rate of crystalgrowth. At temperatures closer to T_(m), the rates are reversed with therate of crystal growth being greater than the rate of crystalnucleation. Processing also impacts polymer crystallinity. Deformationor shear in a polymer melt tends to extend the polymer chains in thedirection of shear or strain. If sufficiently deformed, thecrystallinity may result from strain-induced crystallization as a resultof extension and alignment of the polymer chains.

Biaxial orientation and increased crystallinity may be obtained byradially and axially expanding a polymer tube at controlled temperature.Expansion may be performed at a temperature between T_(g) and T_(m) at atemperature where the rate of crystal nucleation is greater than crystalgrowth. The resulting polymer tube has biaxial orientation andcrystallinity of the desired morphology. In particular, the crystallineregions formed by biaxial orientation have a “shish-kebab form” thatdiffers from the typical spherulitic form that would result fromcrystallization from a quiescent polymer melt. It is believed that theseshish-kebab crystalline regions result in superior mechanical propertiesas compared to the spherulitic form.

Thus, optimization of the strength and fracture toughness of asemicrystalline polymer is not a simple process, but is a complexfunction of both processing and temperature. Careful control of theprocessing and temperature conditions of the polymer allow one to obtaina polymer with the desired morphology, that is the desired crystal size,density, and orientation, to maximize both strength and toughness.Conventional extruded semicrystalline polymer tubes may havecrystallinity due to the manner of processing. The crystallinemorphology of the crystalline regions of the as extruded tube differsfrom the crystallinity formed by the biaxial expansion operation. It isdesirable to have all of the crystalline regions of the desiredmorphology formed in one step in the biaxial expansion. Thus, it isdesirable to start with an extruded polymer tube of low or nocrystallinity which will allow for all the crystallinity of the tube tobe formed in one step under controlled conditions. Ideally, the polymerof the extruded polymer tube would be completely amorphous, but inpractice this is not easily achieved. A stent manufactured from apolymer tube for which the crystallinity is formed in one step isexpected to have superior mechanical properties compared to onemanufactured from a polymer tube for which some crystallinity resultedfrom prior processing such as the extrusion process.

The various embodiments of the present invention provide methods ofextruding a polymer of low crystallinity. Although reference will bemade to a polymer tube, the embodiments of the present invention are notso limited, and all polymer constructs are encompassed. As used herein,“polymer construct” refers to any useful article of manufacture made ofa polymer, a polymer formulation, or a blend of polymers, that is usedas a starting material for further manufacturing steps in thefabrication of a medical device, including an implantable medicaldevice. Non-limiting examples of polymer constructs include a tube, asheet, a fiber, etc. A polymer construct is not a scaffolding structure.

A polymer tube may be used in the fabrication of an implantable medicaldevice, such as a stent. Some of the process operations involved infabricating a polymeric stent may include:

(1) forming a polymeric tube using extrusion;

(2) radially and/or axially deforming the formed tube by application ofheat and/or pressure;

(3) forming a stent from the deformed tube by cutting a stent pattern inthe deformed tube such as with chemical etching or laser cutting;

(4) coating the stent with a coating including an active agent;

(5) crimping the stent on a support element, such as a balloon on adelivery catheter;

(6) packaging the crimped stent/catheter assembly; and

(7) sterilizing the stent assembly.

In some embodiments of the present invention, a method is provided whichresults in the polymer of the extruded polymer tube that is completelyamorphous (100% amorphous, 0% crystallinity) or with very lowcrystallinity, such as less than 5% crystallinity. Embodiments of thepresent invention encompass a crystallinity of not more than 1%, notmore than 2%, not more than 4%, and not more than 5% in the polymer ofthe polymer tube. In some other embodiments, the crystallinity of thepolymer may be greater than 5%, for example between about 5% and about10%. However, a crystallinity of less than 5% is preferred, and isexpected to result in superior mechanical properties of a device, suchas a stent, fabricated from the tube of such a polymer.

As noted above, the tube is typically formed by extrusion. Extrusionrefers to the process of conveying a polymer melt through an extruderand forcing the polymer melt through a die that imparts a selected shapeto the polymer exiting the extruder. FIG. 2 illustrates a typicalextrusion process for extrusion of a polymer tube. The polymer asreceived, typically in the form of pellets or granules, is dried in adryer (201) or hopper dryer before being conveyed to the extruder (202)which melts the polymer to form a polymer melt which is then forcedthrough a breaker plate (203) before being forced through the die whichis part of the die assembly (204) to form a cylindrical film in theshape of a tube. The film is cooled in a water bath (205) and drawnaxially to form the final tube product. Although illustrated as a lineof equipment in FIG. 2, the individual pieces of equipment in theequipment train are not necessarily arranged in a line. Although FIG. 2includes a water bath for cooling, other manners of cooling the extrudedtube may be used and are encompassed within the scope of the presentinvention.

An extruder generally includes a barrel through which a polymer melt isconveyed from an entrance to an exit port. The polymer can be fed to theextruder barrel as a melt or in a solid form below its meltingtemperature. If solid polymer is used, the solid polymer is melted as itis conveyed through the barrel. The polymer in the extruder barrel isheated to temperatures above the T_(m) of the polymer and exposed topressures above ambient (greater than 1 standard atmosphere). Thepolymer within the barrel is conveyed or pumped, for example, throughthe use of rotating screws or a rotating screw. Representativenon-limiting examples of extruders for use with the present inventionmay include single screw extruders, intermeshing co-rotating andcounter-rotating twin-screw extruders and other multiple screwplasticating extruders. A typical single screw extruder has threesections, a feeding section, a compression section, and a meteringsection.

The polymer melt exits the extruder through a breaker plate to a dieplaced at the end of the extruder barrel. The breaker plate, often usedin conjunction with a screen, removes lumps, such as unmelted polymer. Adie generally refers to a device having an orifice with a specific shapeor design geometry that it imparts to a polymer melt pumped from anextruder. In the case of tubing extrusion, the die has a circular-shapedorifice that imparts a cylindrical shape to the polymer melt exiting thedie.

After the polymer leaves the die, it swells due to the fact that, unlikea non-polymeric liquid such as water, the response of a polymer melt toshear has a normal stress component which is due to stored elasticenergy. This normal stress component is no longer constrained by thewall when it exits the die, resulting in die swell. As the polymerleaves the die, it is stretched and drawn down by a conveyor or pullerduring cooling. “Draw down” refers to reducing the size of the polymerby stretching. For example, a tube is stretched longitudinally whichreduces the diameter of the tube. The amount of draw down is defined asthe “draw down ratio,” which is the ratio of the area of the die openingto the final cross-sectional area of the tube. The draw down ratio maybe at least three times the original extruded shape. In someembodiments, the polymeric tube is drawn so that a diameter of theformed tube is less than a target diameter, such as for example, thediameter of a lumen in which the device is intended to be deployed.

Extruded polymer tubes made of semicrystalline polymers may have widelyvariable crystallinity. As used herein, reference to a tube with acrystallinity of X % will mean that the polymer of the tube has acrystallinity of X %. For example, the inventors found that extrusion oftubes of the polyester poly(L-lactide) (PLLA) in a 1″ Killion singlescrew extruder at about 10 RPM, followed by cooling in a water bath,resulted in a polymer tube of 17-24% crystallinity. Variation of theprocessing parameters including the temperature profile of the extruder,screw speed, screw design, tubing cooling rate via changes in thetemperature of the water bath, and the air gap, that is the distancebetween the die exit and the water bath, the puller speed, the airpressure in the extruder, and the area draw down ratio did not result intube with a crystallinity outside the range of 17-24%. Thus, a polymertube of low crystallinity is not easily obtained, and is not obtained byusing just any extrusion equipment and process.

The source of crystallinity in an extruded polymer tube is a complicatedfunction of polymer morphology in the extruder, the rheologicalproperties of the polymer, the conditions in the extruder such as thetemperature and pressure, and the several parameters in the extrusionprocess. The presence of unmelted crystals in a polymer melt exiting adie is one source of crystallinity in a formed polymer tube. Forcomplete removal of the crystalline phase from the polymer, thetemperature should be high enough to melt the crystal, but below atemperature that would degrade the polymer. The melting efficiency canbe facilitated by optimizing screw geometry. Other sources ofcrystallinity in an extruded tube are insufficient homogeneity of thepolymer melt and chain orientation in the polymer melt in the extruder,and/or in the polymer melt exiting the extruder. Quenching of thepolymer film exiting the die may inhibit or prevent crystal growth.Quenching of the film refers to an extremely rapid cooling or extremelyrapid reduction of the temperature of the polymer from a temperatureabove T_(m) of the polymer to below T_(g) of the polymer.

The inventors observed that PLLA tubes extruded using an alternative dieassembly that imparts a spiral flow to the polymer melt unexpectedlyresulted in a tube with a crystallinity of not more than 4% or about 4%.The polymer resin was dried before being extruded in a Killion 1″extruder through the alternative die assembly, and an annular die beforebeing cooled in a water bath at either ambient (about 20 to 25° C.) orchilled (about 15° C. or lower). The extrusion experiments aresummarized in Example 1. It is believed the alternative die assemblyresulted in the lower crystallinity. Although polymer tubes manufacturedfrom such die assemblies were known to exhibit enhancement of bendingstrength and durability, the low crystallinity was unexpected.

The alternative die assembly that was used is a spiral cross-head designof Guill Tool and Engineering. Examples of these die assemblies and/orsubassemblies thereof, are described in U.S. Pat. Nos. 6,902,388, and6,345,972, both of which are incorporated by reference as if fully setforth, including any drawings, herein. The die assembly is designed toprovide a balanced flow through the die. A balanced flow means that thepolymer melt has a uniform temperature and a uniform melt conformation,and is distributed evenly about the circumference of an annular passageway, or extrusion channel, leading to the outlet and the die. An unevendistribution would lead to a tube with variable wall thickness aroundthe circumferences, such as thicker walls on one side of the tube thanthe side that is 180° opposite. In addition, the die assembly, whichincludes the die, is designed such that the polymer melt undergoes aspiral motion as it flows through the die assembly. It is believed thata die assembly or a cross-head die assembly with an even distribution ofthe polymer melt, or an essentially even distribution of the polymermelt, in the flow passage way, and especially one that imparts a spiralor rotational component to the flow of the polymer melt, produces a tubeof low crystallinity, particularly, in the section leading up to thedie, such as less than 5%.

An example of a die assembly useful in performing the methods of thepresent invention is shown in FIG. 3. As illustrated in FIG. 3, thepolymer melt is received at inlet 13 from an extruder outlet 40 and issupplied to a tapered annular extrusion passage way 9. The generalfunction of the die assembly is to receive the polymer melt at theupstream inlet 13 and distribute it to downstream outlet 15 in a flowpattern that is evenly distributed about the extrusion passage way 9.Flow channels that are not shown take the polymer melt from the inlet 13to the grooves 60 in the tip 3 which merge with the annular extrusionpassage way 9 leading to the outlet 15.

The extrusion passage way 9 depicted in FIG. 3 is formed between thesurface 10 of tip 3 and surface 11 of the die holder 4. Tip 3 fits intobore 18 of die body assembly 2. A die 5 may be removably fixed to thedie holder 4 to form a die module and complete the extrusion passage way9, and form the exit 15. A cap 6 keeps the components of the dieassembly securely assembled. The bolts or other fasteners holding thecomponents together are not illustrated in FIG. 3.

The extrusion passage way 9 does not have a constant cross-section. Theannular extrusion passage way is a tapering annular passage way. Thepassage way is essentially the space between two parts in the shape ofconical sections, substantially in the shape of conical sections, or ina shape similar to conical sections. The clearance between surfaces 10and 11 also varies from the upstream end to the downstream end. Thus,for passage way 9 the internal and external radius of the annulus changeand the difference between the internal and external radii also varies.

A continuous flow passage way is formed from inlet 13 to the outlet 15.The polymer melt is received from the extruder at inlet 13. Asillustrated in FIG. 4, a representative and non-limiting top view, thepolymer melt comes in inlet 13, flows down, and is divided into 2primary flow channels 115 and 116. There is a dividing wedge 44 betweenthe two channels to assure even distribution of the flow. The flow maybe subsequently divided again in a like manner to yield 4 secondary flowchannels, and again to form 8 tertiary channels, etc. Alternatively, theflow channel may be divided into 3 channels yielding 6 secondary flowchannels. The primary, secondary, or tertiary, etc. flow channels end ingrooves 60 in the tip 3 depicted in FIG. 3. The polymer melt flowsthrough the grooves to the tapered annular extrusion passage way 9, alsoillustrated in FIG. 3. The polymer melt may be distributed among anumber of flow channels leading to the spiral shaped grooves in anothermanner than that depicted in FIG. 4.

The semi-volute shaped grooves form spiral, or conical helical, flowchannels in the face of the generally conically shaped tip 3. FIG. 5illustrates the grooves 60 in the conical surface 11 of tip 3. The flowchannels are grooves, continuous indentations, engravings, or channelsformed in the surface.

The spiral grooves illustrated in FIG. 5 may be generally expressed bythe mathematical formula for a conical helix. FIG. 6A depicts a helix ofradius a and pitch of 2πb which is represented is mathematically in anx-y-z space as x(t)=a cos(t), y(t)=a sin(t), and z=b(t) where z is theheight and x-y form a plane perpendicular to z. FIG. 6B depicts a helixof pitch 2 n and radius 1 in polar coordinates which is representedmathematically by r(t)=1, z(t)=t, and θ(t)=t. The “pitch” is the heighttraveled in one complete rotation, that is the vertical distancetraveled before x and y return to the initial value, or in polarcoordinates, for θ to return to the initial value. Depicted in FIG. 7 isa conical helix 70 formed on the surface of a cone 19. The differencebetween a helix and a conical helix is that the radius changes for aconical helix as opposed to having a constant value. The conical helix70 shown in FIG. 7 is formed on a cone 19 of slant angle α and height 4n, for which radius, r, at any point is related to the distance alongthe z-axis by tan α. The conical helix of pitch 2π shown in FIG. 7corresponds to the mathematical formula r(t)=(tan α)/t, z(t)=t, andθ(t)=t. If the grooves 60 shown in FIG. 5 are not made in the surface ofa mathematically true cone, the grooves would not form a true conicalhelix, but a similar path in which the radius of the helix varies withthe height of the helix in the same manner as the radius of the tip 3varies with the height of tip 3.

The grooves 60 are arranged symetrically around the circumference of thetip 3. In some embodiments, the number of grooves corresponds to thenumber of secondary, tertiary, etc. flow channels resulting from thedivision of the initial flow of the polymer melt from the extruder. Insome embodiments, one or more of the grooves go completely around thetip, that is at least one complete rotation. In other embodiments, oneor more of the grooves do not completely encircle the tip, that is donot form a complete rotation about the cone, but may cover about ¼ toabout ¾ of a rotation as shown in a top view in FIG. 8A. Preferably thegrooves overlap, that is for the 360° rotation, if one groove starts at0° and ends at 130°, then the next groove would begin at 130° or less,such as 120° as illustrated in FIG. 8B. In some embodiments, one groovestarts at the location around the circumference where a prior grooveends, such as when one groove starts at 0° and ends at 120°, then thenext grooves starts at 120°. In some embodiments, the grooves do notoverlap.

The cross-section of the grooves may be a semi-circle as depicted inFIG. 9A, essentially a semi-circle, or a circular segment, as depictedin FIG. 9B. The cross-section of the grooves may be other shapes. Theremay be similar mating grooves 80 in the surface of die holder 4 and dieassembly body 2 such that when put together the grooves form a flowchannel as illustrated in FIG. 9C. If the grooves are semi-circles inboth die holder 4 and die assembly body 2, the flow channel formed is ofcircular cross-section. The combination of the surfaces forms theextrusion channel leading to the annular extrusion passage way 9. Thegrooves gradually taper as they move downstream, that is thecross-sectional area decreases in the direction of polymer flow,eventually reaching zero.

The spiral die assembly provides both a balanced flow and imparts aspiral or rotational component to the velocity of the polymer melt. Itis believed that the tapering of the spiral grooves imparts a spiralflow or rotational velocity component to the polymer melt. The dieassembly is intended to take molten polymer from the extruder and forceit through a die, which is essentially an annulus, to form a hollowtube. The approximate shape of the flow passage way is illustrated FIG.10 with a polar coordinate system. The z-axis is at the center of thedie, and lies along the axis of the conical tip 3. At point A in FIG. 10which is within a spiral flow channel, the velocity of the polymer melthas components in the z—direction, that is the polymer melt is flowingdownstream to the annulus at the outlet. There is also a radialcomponent inward as the flow passage way tapers to an annulus of asmaller diameter at the outlet. In addition, there is a azimuthalcomponent θ, or rotational component. The azimuthal component is aresult of forcing the polymer melt through the flow channels. It isbelieved that the low crystallinity results at least in part due to therotational or azimuthal component of the flow in the section of theannular portion of the die assembly, and particularly if the rotationalcomponent of the flow occurs in a section just prior to or leading up tothe die outlet.

The tapering spiral grooves also ensure a balanced flow of polymer meltin the annular portion of the die assembly. Balanced flow ensurespolymer melt homogeneity. The polymer melt is forced through the spiralgroove 60 in direction shown in FIG. 11 by arrow 44. As the groovestaper and merge with the annular extrusion passage way, some of thepolymer melt is forced over the side of the grooves as illustrated inFIG. 11 by arrow 45. Thus, at the point where the grooves initiallymerge with the annular passage way 9, the polymer melt is at a highpressure and the clearance between surfaces 10 and 11 (see FIG. 3), orthe width of the annular passage way 9, is small. The clearanceincreases as the grooves taper. As the polymer flows through thechamber, pressure losses result in a lower pressure further downstream.As a result, the tapering of the grooves and the increase in theclearance facilitate the even distribution of the polymer melt aroundthe circumference of the annular passage way. The fact that theclearance is smaller upstream where there is a higher pressure limitsthe amount of polymer forced over the side, while further downstreamwhere the pressure is lower, the clearance increases and the groovedepth decreases, allowing approximately the same amount of polymer to goover the side of the channel.

Balanced flow means the polymer melt is distributed evenly around thecircumference of the passage way, and that the melt has a uniformtemperature and a uniform melt conformation. As FIG. 12. illustrates atop-view of annular passage way 9, the mass flow rate of polymer meltthrough a circular section 99 of angle A is the same, or substantiallythe same, as the mass flow through any other circular section of angleA, such as that of section 98. If the polymer flow is unevenlydistributed, the wall of the tube extruded may vary in thickness aroundit's circumference.

It is believed that the combination of the balanced flow and the spiralor rotational flow result in the polymer tube of low crystallinity.Generally, the application of shear to a polymer melt results inorientation of the polymer chains in the direction of the shear. Thus,the polymer chains are in an extended configuration. If the polymerchains are in an extended configuration as they exit the die, the chainsare more likely to crystallize when quenched than if the polymer chainsare in a random coil configuration, a state in which the chains are notextended. It is entropically more favorable for rigid linear molecules,or rigid rods, to align and form a crystalline region, than to assume arandom orientation with respect to each other. If the extended chains donot relax to their random coil configuration prior to quenching, thepolymer chains are essentially rigid rods and crystallization isfavored. If the polymer melt is subjected to further strain such as bypulling, the probability of crystallization increases. The stretching ofpolymer chains, such as in a draw down process, to form any chainorientation before/after exiting the die would cause strain-inducedcrystallization upon solidification of the polymer.

It is believed that the spiral flow, or rotational motion of the polymermelt, results in the chains exiting the die in a configuration that isthe random coil configuration, or a configuration that is close to therandom coil configuration, in contrast to a configuration in which someof the chains are in the extended chain configuration. The relaxationtime of the polymer melt, that is the time frame for the polymer toreturn to its relaxed or unconstrained random coil configuration can bedetermined using a capillary viscometer. Use of the spiral cross-headproduced a polymer melt with a relaxation time that was significantlyless than the polymer melt produced previously with the conventionalequipment which did not have spiral flow channels. Therefore, it can beinferred that the polymer chains are closer to their random coilconfiguration. It is believed that the flow in the helical grooves isanalogous to the rifling action in a gun barrel and imparts a spiralflow to the polymer melt. It is believed that the azimuthal component ofthe velocity of the polymer melt in the annular region of the dieassembly prevents the chains from being fully extended along the z-axis,and as a result the chains are closer to the random coil configuration.

Further the spiral grooves confine the polymer within the groove untilthe grooves merge with the tapered annular extrusion passage way. Whenthe tapered grooves merge with the annular extrusion chamber, thepolymer melt begins to spill over the edge of the groove into theannulus and thus the direction of polymer flow changes as describedabove and illustrated in FIG. 11. It is also believed that this changein polymer flow direction helps prevent the full extension of thepolymer chains. In some embodiments, the melt relaxation time of thepolymer melt as it exits the die may be less than 90 seconds, preferablyless than 60 seconds, or more preferably, less than 45 seconds.

The spiral flow cross-head die assembly provides for improved mixing ofthe polymer melt with fewer dead spots, that is spots in the passage wayin which the polymer melt is stagnant. It is also believed that thespiral flow and the balanced flow result in a polymer melt that is moreuniform in temperature. It is believed that the improved mixing and moreuniform temperature of the polymer melt may allow for a lowertemperature in the extruder and a lower compression ratio, that is theratio of the channel depth of the extruder in the feeding section to thechannel depth at the end of the compression section or the beginning ofthe metering section. The channel depth in the extrusion chamber isessentially the height of the screw flight for a single screw extruder.The lower temperature, and lower shear which is consequence of the lowercompression ratio, results in less polymer degradation during theextrusion process. The polymer melt residence time in the spiralcross-head die assembly is lower than that of the previously usedconventional die assembly, also resulting is less polymer degradation.

The lower crystallinity polymer tube produced may be a polymer constructfrom which an implantable medical device, such as a stent, may befabricated. It is expected that the lower crystallinity of the extrudedpolymer tube may result in a polymeric device, such as a stent, withimproved and more consistent mechanical properties. It is important thatthe crystallinity is formed in one step and at the same time during thebiaxial deformation. The extruded tubes made with conventional equipmentnot only included about 17% to 24% crystallinity, but the crystalsformed were of a spherulitic form. Improved mechanical properties mayresult from careful control of the orientation and size of thecrystalline regions in the polymer that are formed in the expansionprocess. It is believed that a shish-kebab form for the crystallineregions that results from the bi-axial expansion of the tube providessuperior mechanical properties as compared to the spherulitic form.Thus, it is of critical importance that the initial extruded polymertube have little or no crystallinity.

The shish-kebab crystalline regions result from controlled axial andradial expansion of the extruded polymer tube at a controlledtemperature below the T_(m), and preferably between T_(g) and T_(m). Thedegree of radial deformation may be quantified by a blow-up ratio orradial draw ratio, expressed as a percent by:

$\frac{100*{Inside}\mspace{14mu} {Diameter}\mspace{14mu} {of}\mspace{14mu} {Deformed}\mspace{14mu} {Tube}}{{Original}\mspace{14mu} {Inside}\mspace{14mu} {Diameter}\mspace{14mu} {of}\mspace{14mu} {Tube}}$

In some embodiments, the radial draw ratio of a polymeric tube for usein fabricating a stent may be between about 100% to 500%. Similarly, thedegree of axial deformation may be quantified by an axial draw ratio,expressed as a percent by:

$\frac{100*{Length}\mspace{14mu} {of}\mspace{14mu} {Deformed}\mspace{14mu} {Tube}}{{Original}\mspace{14mu} {Length}\mspace{14mu} {of}\mspace{14mu} {Tube}}$

In some embodiments the radial and axial deformation of the formed tubeis such that that the deformed tube is of a target diameter, such aswithout limitation, the diameter of a lumen. Careful control of the rateof deformation and the temperature during deformation allows for controlof the crystal growth so that the tube has the desired morphology asdescribed above.

Another advantage of a polymer construct that is amorphous or very lowcrystallinity, is that it provides for greater reproducibility of afinal processed polymer construct with respect to microstructure andmechanical properties. Microstructure includes crystal size, crystaldensity, crystal orientation, amorphous orientation, and crystal shape.Preferably, all the crystallinity is developed in one step, duringdeformation and/or expansion. Thus, it is preferable to start with atube which is amorphous, or substantially amorphous.

As a non-limiting example a polymer tube may be extruded from PLLA wherethe PLLA is heated and mixed in the extruder to form a polymer meltbefore being extruded though an annular die that is part of a dieassembly. The die assembly may be a spiral cross-head die assembly. Theextruder may be operated at a compression ratio in the range of about3.5:1 to about 2.75:1, and at a temperature in the range about 190° C.to about 225° C., or more narrowly, from about 190° C. to about 215° C.The temperature at the die outlet or within the die assembly may be fromabout 200° C. to about 230° C. The pressure in the extruder and dieassembly may reach a maximum from about 4500 psi to about 5500 psi. Uponexiting the die, the polymer film may be drawn, and subsequentlyquenched, such as by being passed through a water bath at ambient (20°C. to 25° C.) or slightly chilled (10° C. to 15° C.). The formed polymertube may have a crystallinity of less than 5%, or less than 4%, asdetermined by differential scanning calorimetry (DSC). The polymer tubeof PLLA may be expanded at a temperature in the range of from about 60°C. to about 100° C., or from about 60° C. to about 80° C. The radialexpansion under controlled temperature conditions is performed toincrease the radial strength of the polymer tube and to increase thecrystallinity of the polymer tube to about 20% to about 50%, or to about30% to 45%. In some embodiments, the polymer tube may be both axiallyand radially expanded. A stent may be formed from the expanded PLLAtube. As another non-limiting example, the above process may be carriedout with poly(L-lactide-co-glycolide) of 85 mol % lactide, and 15 mol %glycolide.

It is believed that the use of a die assembly which imparts a spiralflow or a rotational component to the velocity of the polymer melt mayprovide an extruded tube of low crystallinity, that is less than 5% orabout 5%, for any semicrystalline polymer that is susceptible to straininduced crystallization. Representative semicrystalline polymers thatmay be used in embodiments of the present invention include, withoutlimitation, polymers formed from L-lactide, glycolide, or combinationsthereof such as 85 mol % lactide and 15 mol % glycolide, PLLA,polyglycolide (PGA), poly(L-lactide-co-glycolide) (PLGA),poly(L-lactide-co-caprolactone) (PLCL), and PLLA-b-poly(ethylene oxide)(PLLA-b-PEO).

Representative examples of other polymers that may be used in thevarious embodiments of the present invention, if they are subjected tostrain induced crystallization, include, without limitation:poly(hydroxybutyrate), polyorthoesters, polyanhydrides, poly(glycolicacid), poly(glycolide), poly(L-lactic acid), poly(L-lactide),poly(D-lactic acid), poly(D-lactide), poly(caprolactone),poly(trimethylene carbonate), polyester amide, polyesters, polyolefins,polycarbonates, polyoxymethylenes, polyimides, polyethers, andcopolymers and combinations thereof.

As used herein, the following definition apply:

As used herein, when reference is made to a polymer having X mol % of aparticular monomer such refers to the mole percent of the monomer usedto form the polymer.

The “glass transition temperature,” T_(g), is the temperature at whichan amorphous polymer or the amorphous domains of a semicrystalline orblock co-polymer change from a brittle, vitreous state to a soliddeformable state (or rubbery state) at atmospheric pressure. In otherwords, the T_(g) corresponds to the temperature where the onset ofsegmental motion in the backbone chains of the polymer occurs. Themeasured T_(g) of a given polymer can be influenced by the thermalhistory, and potentially pressure history, of the polymer, as well asthe parameters utilized to measure the T_(g), such as the pressure atwhich the measurement is made and the heating rate in differentialscanning colorimetry (DSC). T_(g) is a function of the chemicalstructure of the polymer, but is also affected by other compounds mixedwith the polymer, whether it is a filler, solvent, etc.

The “melting temperature,” T_(m), of a polymer is the temperature atwhich an endothermal peak is observed in a DSC measurement, and where atleast some of the crystallites begin to become disordered. The measuredmelting temperature may occur over a temperature range as the size ofthe crystallites, as well as presence of impurities and/or plasticizers,impacts the measured melting temperature. Crystalline domains are thosein which polymer chains adopt an ordered orientation with segments ofseparate chains or of the same chain becoming essentially parallel toone another to form structures known as lamellae. Lamellae initiallyform from a point of nucleation. The formed lamellae then grow outwardfrom the nucleation point to form larger, essentially sphericalcrystalline structures known as crystallites.

As used herein, a reference to the crystallinity of a polymer refers tothe crystallinity as determined by standard DSC techniques with aheating rate of 20° C./min. For PLLA, it is assumed that a perfectcrystal has a heat of fusion of 93.7 joules per gram.

A “polymer melt,” refers to a semicrystalline polymer that has no orsubstantially no crystallites and is at or above the meltingtemperature, or for an amorphous polymer, is at a temperaturesufficiently high enough above the glass transition temperature that itmay be processed. As used herein a polymer melt is not necessarily 100%polymer but may include additives such as stabilizers, plasticizers,etc.

As used herein a construct, tube, etc which is said to be “fabricatedfrom a polymer” or reference is made to a polymer construct, polymertube, or polymeric tube or the like, the item so modified is made from apolymer, a blend of polymers, a material for which one or more polymersforms a continuous phase, or a material for which one or more polymerscomprises at least 50% by volume of the material.

“Strength” refers to the maximum stress along an axis which a materialwill withstand prior to fracture. The ultimate strength is calculatedfrom the maximum load applied during the test divided by the originalcross-sectional area.

“Modulus” may be defined as the ratio of a component of stress or forceper unit area applied to a material divided by the strain along an axisof applied force that results from the applied force. The modulustypically is the initial slope of a stress—strain curve at low strain inthe linear region. For example, a material has a tensile, a compressivemodulus, and a storage or shear modulus.

“Toughness” is the amount of energy absorbed prior to fracture, orequivalently, the amount of work required to fracture a material. Onemeasure of toughness is the area under a stress-strain curve from zerostrain to the strain at fracture. The units of toughness in this caseare in energy per unit volume of material. See, e.g., L. H. Van Vlack,“Elements of Materials Science and Engineering,” pp. 270-271,Addison-Wesley (Reading, Pa., 1989).

“Polymer melt relaxation” time as used herein is that determinedutilizing a capillary viscometer. The polymer melt is forced out of thecapillary with a piston at a temperature and pressure corresponding toextrusion conditions. Once these conditions have equilibrated in therheometer, the piston movement is stopped. The melt relaxation time isdefined as the time that it takes for the pressure to decay to 20% ofits original value.

The terms “biodegradable,” “bioabsorbable,” and “bioerodable” are usedinterchangeably and refer to polymers and/or other materials that arecapable of being completely degraded and/or eroded when exposed tobodily fluids such as blood and can be gradually resorbed, absorbed,and/or eliminated by the body. The processes of breaking down andabsorption of the polymer can be caused by, for example, hydrolysis andmetabolic processes. Biostable refers to polymers and/or materials thatare not biodegradable.

As used herein, the terms poly(D,L-lactide), poly(L-lactide),poly(D,L-lactide-co-glycolide), and poly(L-lactide-co-glycolide) areused interchangeably with the terms poly(D,L-lactic acid), poly(L-lacticacid), poly(D,L-lactic acid-co-glycolic acid), and poly(L-lacticacid-co-glycolic acid), respectively.

EXAMPLES

The examples set forth below are for illustrative purposes only and arein no way meant to limit the invention. The following examples are givento aid in understanding the invention, but it is to be understood thatthe invention is not limited to the particular examples. The parametersand data are not to be construed to limit the scope of the embodimentsof the invention.

Example 1

A number of extrusion trials were run with poly(L-lactide) to produceextruded polymer tubes. Poly(L-lactide) (PLLA), RESOMER® L 210 S,supplied by Boehringer Ingelheim, was used. The PLLA had a weightaverage molecular weight in the range of about 590,000 to about 650,000,a number average molecular weight in the range of about 320,000 to about380,000, a crystallinity of about 60%, an inherent viscosity of 3.3-4.3dL/g as determined in chloroform at 25° C. and a 0.1% (mass/volume)concentration, and a water content of less than or equal to 0.5%. ThePLLA resin was dried in an on-line hopper using air at 60° C. and about0% humidity resulting in a residual moisture content of less than 200ppm. After being dried in the hopper, the PLLA was gravity fed to theextruder. The PLLA was extruded in a 1″ inch Killion single screwextruder with a length to diameter ratio of 24 using a compression ratioof 3.27:1, and a speed (extruder screw) ranging from 5 to 15 RPM. Thethree zones of the extruder were set to 410° F. and the pressure in theextruder ranged from 2000 psi to 5100 psi with the 5100 psi occurring atthe end of the third zone.

At the end of the extruder, the polymer melt was forced through abreaker plate prior to going through the spiral-cross-head die assembly.The spiral cross-head was manufactured by Guill Tool and Engineeringcompany and was a Model 712 Crosshead, an earlier version than the 712Model Assembly of Example 2. The die used had a 0.179″ diameter. Thetemperature in the die and cross head assembly was about 430° F., andthe pressure at the die exit was about 200 to about 700 psi.

The extruded film was drawn at a ratio ranging from 4 to 10 and cooledin a vacuum size chilled water bath at ambient temperature (about 20 to25° C.) with a residence time in the water bath of about 30 seconds orless than 30 seconds. The air gap between the die exit and the waterbath varied from 0 to 2″.

Analysis of the thermal properties of a number of the polymer tubes(sample size of three for each test run) are summarized in Table 1. Thedata was obtained using a Differential Scanning calorimeter at a heatingrate of 20° C./min, with a flow of an inert and calibrated with anIndium standard. Crystallinity was determined based upon the area of thecrystalline melting peak with 93.7 joules/gram as the reference valuefor a 100% crystalline PLLA polymer.

TABLE 1 Thermal Analysis Results for Polymer Tubes Standard Test RunStandard Average Deviation % Number Average Tg Deviation Tg %Crystallinity Crystallinity 8 57.62 0.13 3.90 1.61 9 57.93 0.29 6.851.19 10 58.01 0.25 6.67 1.46 1 56.14 1.05 1.27 0.39 7 57.73 0.77 1.061.36 16 57.43 0.44 0.7 0.08

As shown in Table 1, all of these samples exhibited crystallinity under10%, with some samples exhibiting crystallinity of less than 2%.

Example 2

The following prophetic example illustrates the extrusion of a polymertube on slightly different equipment. Extrusion of PLLA as described inExample 1 is performed. The polymer resin is dried using a hopper/dryeras described in Example 1. The extruder used is a ¾″ American KhuneExtruder with a barrier screw, three feed flights, and a length todiameter ratio of 24:1. The extrusion is carried out at a compressionratio of 3:1 and a speed in the range of 5 to 30 RPM. The temperature inthe extruder is about the same as or slightly lower than thetemperatures used in Example 1.

At the end of the extruder, the polymer melt is forced through a breakerplate and into the spiral cross-head die assembly. The spiral cross-headis manufactured by Guill Tool and Engineering company and is a Model 712Assembly which was selected for use with poly(L-lactide). The Model 712Assembly primarily differs from that of example 1 in that the tip(analogous to reference numeral 3 in FIG. 3) is slightly different,being part Guill Tool and Engineering part No. 71203058 versus part No.71203067. A die of 0.179″ diameter is used. The temperature and pressureis about the same as in Example 1.

The extruded film is drawn and quenched as described in Example 1. Thecrystallinity of the resulting polymer tube is determined by DSC.

While particular embodiments of the present invention have been shownand described, it will be obvious to those skilled in the art thatchanges and modifications can be made without departing from thisinvention in its broader aspects. Therefore, the appended claims are toencompass within their scope all such changes and modifications as fallwithin the true spirit and scope of this invention.

1-20. (canceled)
 21. A stent comprising: a cylindrically-shaped scaffoldincluding a biodegradable polymer having a pattern of a plurality ofinterconnecting struts formed from a polymeric tube comprising thebiodegradable polymer, wherein the biodegradable polymer of the polymertube has a crystallinity of 20% to 50 the crystallinity comprisescrystals of a spherulite form and a shish-kebob form with less than 5%of the crystals being of the spherulite form, wherein the stent isexpandable within an anatomical lumen of a body.
 22. The stent of claim21, wherein 15% to 45% of the crystallinity is of the shish-kebob form.23. The stent of claim 21, wherein the biodegradable polymer of thepolymer tube comprises a crystallinity of 30% to 45%.
 24. The stent ofclaim 21, wherein 25% to 40% of the crystallinity is of the shish-kebobform.
 25. The stent of claim 21, wherein the polymer comprisespoly(L-lactide).
 26. The stent of claim 21, wherein the polymercomprises poly(L-lactide-co-glycolide).
 27. The stent of claim 26,wherein the poly(L-lactide-co-glycolide) is 15 mol % L-lactide and 85%glycolide.
 28. The stent of claim 21, wherein the polymer comprisespoly(L-lactide-co-caprolactone).
 29. The stent of claim 21, wherein thepattern is formed by cutting the pattern in the polymer tube.